Power supply for tissue ablation, cutting and fusion system and tissue ablation, cutting and fusion system

Abstract

The present invention discloses a power supply for a tissue ablation, cutting, and fusion system. The power supply outputs a low-frequency DC pulse voltage with a high-level voltage below 24V and a frequency below 500Hz. The duty cycle of the DC pulse voltage output by the power supply can be adjusted based on the thermal conductivity of the tissue to be ablated, cut, or fused. The tissue ablation, cutting, and fusion system of the present invention comprises a power supply for a tissue ablation, cutting, and fusion system of the present invention. The tissue ablation, cutting, and fusion system of the present invention comprises a handle assembly, a shaft assembly, a working portion, a circuit system, and a power supply. The DC pulse voltage output by the power supply periodically switches between high and low levels to cyclically power on and off the electric heating device, maintaining the heating device in a state of heating when powered on and moderate cooling when powered off. This ensures that as heat is continuously transferred deep into the tissue or organ, the temperature at the site of contact between the heating device and the tissue or organ remains within a stable range and does not continue to rise. This effectively prevents accidental damage to the tissue or organ caused by excessive temperatures, making clinical use safer and more reliable.

Description

Technical Field

[0001] The present invention relates to a power supply for an electrosurgical instrument and the electrosurgical instrument, in particular to a surgical instrument used for tissue ablation, cutting and fusion in surgical operations and a power supply thereof. Background Art

[0002] In surgical operations, tissue ablation, cutting and fusion are very important tissue processing processes. Among the currently commonly used tissue ablation, cutting and fusion technologies, high-frequency electrosurgery, radiofrequency ablation and electric heating tissue ablation are all methods. In particular, electric heating tissue ablation is an important method. By heating the tissue, protein modification occurs, thereby achieving tissue ablation, cutting and fusion processes.

[0003] In existing tissue ablation, cutting, and fusion systems, continuous heating is typically used to maintain the temperature of the working portion during the ablation, cutting, or fusion process. However, heat conduction through tissues or organs takes time. Therefore, there is often a significant time lag between the time the working portion contacts the tissue or organ and the temperature deep within the tissue reaches the required operating temperature. This time lag can cause the contact area to overheat due to continuous heating during clinical practice, leading to accidental high-temperature burns to the tissue or organ in contact.

[0004] Therefore, there is a need to improve the tissue ablation, cutting and fusion systems of the prior art, and in particular, to further improve the power supply systems thereof to match the time requirement for heat conduction in the tissue. Summary of the Invention

[0005] The tissue ablation, cutting and fusion system of the present invention is specially designed with a low-voltage DC pulse voltage system. The power supply system outputs a safe DC pulse voltage lower than 24V. By adjusting the frequency and duty cycle of the DC pulse voltage output by the power supply system, the continuous heating method in the existing technology can be converted into an intermittent pulse heating method, and the time ratio of power on and power off can be controlled to meet the requirements of different thermal conduction time differences caused by different thermal conductivities of different tissues. While the heat emitted by the heating element is continuously conducted to the deep layer of the tissue, the intermittent heating method can keep the temperature of the contact part always within a safe temperature range, which can effectively avoid accidental tissue damage caused by excessive temperature of the contact part caused by the existing continuous heating method, and is safer and more reliable during clinical use.

[0006] The present invention provides a power supply for a tissue ablation, cutting, and fusion system, characterized in that the power supply 500 is a low-voltage power supply having an output voltage of less than 24V. The output voltage of the power supply 500 is a safe voltage of less than 24V, and even if an unexpected phenomenon such as leakage occurs during use, it will not cause accidental harm to the human body.

[0007] Preferably, the output voltage of the power supply 500 is less than 12V.

[0008] The power supply 500 is a DC pulse power supply 501. The DC pulse voltage output by the power supply 500 periodically switches between high and low levels to periodically power on and off the electric heating device 32, maintaining the electric heating device 32 in a state of power on for heating and power off for moderate cooling. This ensures that as heat is continuously conducted deep into the tissue or organ 9, the temperature of the area where the heating device contacts the tissue or organ 9 remains within a stable range and does not continue to rise, effectively preventing accidental damage to the tissue or organ 9 due to excessive temperature, making clinical use safer and more reliable.

[0009] The frequency of the DC pulse voltage output by the DC pulse power supply 501 is less than 500 Hz. According to the thermal conductivity of tissues and organs, the DC pulse power supply 501 usually outputs a low-frequency DC pulse voltage with a frequency of less than 500 Hz. On the one hand, low-frequency pulses can increase the range of high-level and low-level durations, ensuring sufficient heat conduction time while also giving the heating device 32 sufficient cooling time to ensure that the temperature of the heating device 32 can be controlled within a safe temperature range. At the same time, low-frequency pulses can better avoid electromagnetic interference that may be caused by electromagnetic pulses to peripheral equipment during instrument operation, and the electromagnetic compatibility of the instrument is better.

[0010] Furthermore, the frequency range of the DC pulse voltage output by the DC pulse power supply 501 is 3 Hz to 200 Hz.

[0011] The duty cycle of the DC pulse voltage output by the DC pulse power supply 501 is adjustable.

[0012] The duty cycle of the DC pulse voltage output by the DC pulse power supply 501 is adjusted according to the thermal conductivity of the tissue or organ 9 that needs to be ablated, cut, or fused.

[0013] Depending on the thermal conductivity of the tissue being ablated, cut, or fused, the required power output of the heating device 32 also varies. Consequently, the duty cycle of the DC pulse voltage output by the DC pulse power supply 501 also varies. This means that the heating time and power-off time of the heating device 32 need to be adjustable based on the target tissue. The duty cycle of the DC pulse voltage output by the power supply for a tissue ablation, cutting, and fusion system of the present invention is adjustable to meet the thermal conductivity requirements of different tissues or organs 9.

[0014] The output current of the power supply 500 is less than 10A.

[0015] The power source 500 is a battery module 51, a battery pack module 52, or a main unit 53. The battery module 51 or battery pack module 52 is small and lightweight, suitable for portability, has low power requirements, and offers a safer low-voltage power supply. The main unit 53 provides stable power supply for extended periods, making it particularly suitable for long, large-scale surgeries. Users can select different power sources 500 based on their specific environment and requirements.

[0016] The tissue ablation, cutting and fusion system of the present invention includes the power source 500 .

[0017] The tissue ablation, cutting and fusion system of the present invention is characterized by:

[0018] A. The tissue ablation, cutting and fusion system 900 includes a handle assembly 100, a shaft assembly 200, a working portion 300, a circuit system 400 and a power supply 500;

[0019] B. The handle assembly 100 includes a trigger assembly 11, a gear adjustment button 12, a shaft connection mechanism 13, and a housing 14; the trigger assembly 11, the gear adjustment button 12, and the shaft connection mechanism 13 are disposed on the housing 14;

[0020] C. The shaft assembly 200 includes a shaft 21 and a connecting assembly 22;

[0021] D. The working portion 300 includes at least two working surfaces 31 , and at least one of the working surfaces 31 is provided with an electric heating device 32 ;

[0022] E. The circuit system 400 includes a circuit 41, a controller 42, and an electrical interface device 43; the circuit system 400 is connected to the power supply 500 via the electrical interface device 43;

[0023] F. The proximal end of the shaft assembly 200 is connected to the handle assembly 100 via the shaft connection mechanism 13; the distal end of the shaft assembly 200 is connected to the working part 300; and the electric heating device 32 is connected to the power supply 500 via the circuit system 400.

[0024] The controller 42 includes a trigger switch 42 - 1 ; movement of the trigger assembly 11 can turn the trigger switch 42 - 1 on or off.

[0025] The tissue ablation, cutting and fusion system of the present invention can only turn on the trigger switch 42-1 and heat the electric heating device 32 by pulling the trigger assembly 11 to apply working pressure to the working part 300, thereby avoiding accidental injuries or safety hazards that may be caused by misoperation, and the clinical use process is safer and more reliable.

[0026] The handle assembly 100 also includes a fixing mechanism 15; the trigger assembly 11 is fixedly mounted on the housing 14 via the fixing mechanism 15. During assembly, the trigger assembly 11 can be embedded or fixed in the mounting groove of the fixing mechanism 5, and then fixed to the housing 14 after being assembled into a whole, which simplifies the assembly process and provides a more secure fixation.

[0027] The trigger assembly 11 includes a trigger 11-1, a rocker arm 11-2, and a slider 11-3; the trigger 11-1 is provided with a trigger shaft 11-1-1 and a rocker arm drive shaft 11-1-2; the rocker arm 11-2 includes a rocker arm fulcrum 11-2-1, a motion slide 11-2-2, and a push block slot 11-2-3; the slider 11-3 includes a motion push block 11-3-1, a sliding convex step 11-3-2, and a working boss 11-3-3; The trigger shaft 11-1-1 and the fixing mechanism 15 are connected together and fixed on the housing 14; one end of the rocker arm drive shaft 11-1-2 is connected to the trigger 11-1, and the other end is embedded in the motion slot 11-2-2; the rocker arm fulcrum 11-2-1 and the fixing mechanism 15 are connected together, so that the rocker arm 11-2 is movably installed in the housing 14; the motion push block 11-3-1 is embedded in the push block slot 11-2-3, and the sliding convex step 11-3-2 is embedded in the positioning slot 15-1 of the fixing mechanism 15 and is connected to the fixing mechanism 15; pull the trigger 11-1, The trigger 11-1 rotates around the trigger shaft 11-1-1, driving the rocker drive shaft 11-1-2 to reciprocate along the motion slot 11-2-2, thereby pushing the rocker 11-2 to swing back and forth around the rocker fulcrum 11-2-1; the reciprocating swing of the rocker 11-2 pushes the motion push block 11-3-1 embedded in the push block slot 11-2-3, thereby driving the slider to move back and forth in a straight line along the positioning slot 15-1, thereby realizing the closing and opening of the working surface 31 of the working part 300.

[0028] A trigger portion 11-1-3 is provided on the trigger 11-1; when the trigger 11-1 moves toward the handle 14-1 of the shell 14, the trigger portion 11-1-3 touches the trigger switch 42-1, and the trigger switch 42-1 is turned on; when the trigger 11-1 moves away from the handle 14-1 of the shell 14, the trigger portion 11-1-3 disengages from the trigger switch 42-1, and the trigger switch 42-1 is turned off.

[0029] The gear adjustment button 12 is connected to the controller 42 via the line 41. Doctors can select different output powers through the gear adjustment button 12 according to the specific circumstances of the surgical process, making clinical operation more convenient.

[0030] The gear adjustment button 12 includes a cutting gear 12-1 and a fusion gear 12-2. The cutting gear 12-1 and the fusion gear 12-2 are linked together by a lever mechanism 12-3, so that the cutting gear 12-1 and the fusion gear 12-2 cannot be pressed at the same time. This prevents the cutting gear 12-1 and the fusion gear 12-2 from being pressed at the same time, thereby preventing misoperation during clinical use.

[0031] The handle assembly 100 also includes a reset mechanism 16. When the trigger 11-1 is released, the reset mechanism 16 automatically resets the trigger 11-1 through a reset force, significantly improving the safety, convenience, and comfort of use. The reset mechanism 16 can be in various forms, such as a torsion spring mechanism, a spring mechanism, or an elastomeric mechanism. Those skilled in the art can design various reset mechanisms as needed, and can install one or more reset mechanisms 16 in different locations on the device as needed without departing from the scope of protection of this application.

[0032] The handle assembly 100 also includes a force-limiting mechanism 17. The force-limiting mechanism 17 can limit the working pressure transmitted to the working part 300 through the trigger assembly 11. When the force-limiting mechanism 17 takes effect, the maximum working pressure applied to the working part 300 after the operator pulls the trigger 11-1 is constant. Usually, during the ablation, cutting and fusion of soft tissues, the maximum working pressure can be limited to below 100N. Of course, those skilled in the art can set the limit value of the maximum working pressure limited by the force-limiting mechanism 17 as needed, which does not deviate from the scope of protection of this application. The force-limiting mechanism 17 can be a spring force-limiting mechanism, an elastomer force-limiting mechanism, a compression spring force-limiting mechanism or other forms of structures. Those skilled in the art can also design other various forms of force-limiting mechanisms, which do not deviate from the scope of protection of this application.

[0033] The trigger switch 42-1 can only be activated when the trigger 11-1 moves toward the handle 14-1 of the shell 14 until the force limiting mechanism 17 takes effect. When the trigger switch 42-1 is in the on state, the gear adjustment button 12 can be closed and the circuit system 400 can be connected to enable the tissue ablation, cutting or fusion system 900 to perform tissue ablation, cutting or fusion under the set working pressure. Because the trigger switch 42-1 can be activated only when the force-limiting mechanism 17 takes effect, it is ensured that the working pressure applied to the tissue by the doctor during the operation is constant, so that the tissue ablation, cutting and fusion system of the present invention can only perform tissue ablation, cutting or fusion under the set working pressure, the surgical effect is more stable, and it effectively prevents accidental injuries that may be caused by misoperation, as well as clinical effects such as blood vessel closure, tissue fusion, and cutting that are different due to the different clamping forces used by different surgeons. It is safer and more effective. That is, a tissue ablation, cutting and fusion system of the present invention can only be activated to perform tissue ablation, cutting and fusion under a constant clamping force, avoiding differences in the use effect caused by different forces used by the operator.

[0034] The shaft assembly 200 further includes a knob 23 ; the knob 23 can drive the shaft 21 to rotate.

[0035] The shaft 21 includes an inner rod 21-1 and an outer rod 21-2; the working surface 31 is connected to the distal ends of the inner rod 21-1 and the outer rod 21-2 respectively; when the inner rod 21-1 moves toward the proximal end, the working surface 31 is closed; when the inner rod 21-1 moves toward the distal end, the working surface 31 is opened; turning the knob 23 can drive the inner rod 21-1 and the outer rod 21-2 to rotate, thereby driving the working surface 31 to rotate.

[0036] During clinical use, the working surface 31 often needs to be rotated to a suitable position according to the different parts of the tissue to be treated. The knob 23 can drive the shaft 21 to move, thereby driving the working surface 31 to rotate to a suitable direction and position.

[0037] The electrical interface device 43 is an elastic electrical interface device 431, which includes a conductive connector 43-1, an elastic conductive mechanism 43-2 and an electrical interface 43-3; one end of the conductive connector 43-1 is connected to the electric heating device 32 through the line 41, and the other end is connected to the elastic conductive mechanism 43-2; the other end of the elastic conductive mechanism 43-2 is connected to the electrical interface 43-3, and the electrical interface 43-3 is connected to the power supply 500.

[0038] The conductive joint 43-1 includes a rotor 43-1-1 and a stator 43-1-2; the rotor 43-1-1 can rotate; the distal end of the rotor 43-1-1 is connected to the proximal end of the shaft 21, and when the shaft 21 rotates, the rotor 43-1-1 can rotate synchronously; the proximal end of the stator 43-1-2 is connected to the distal end of the elastic conductive mechanism 43-2.

[0039] Since the rotor 43-1-1 can rotate synchronously with the shaft 21, the line 41 connecting the rotor 43-1-1 and the shaft 21 also rotates synchronously. The line 41 connecting the conductive connector 43-1 and the rear end of the shaft 21 remains synchronized, thereby avoiding the breakage of the wires or the loosening of the solder joints caused by the twisting of the line 41.

[0040] The elastic conductive mechanism 43-2 is a conductive mechanism that can elastically deform under external force while maintaining a smooth circuit. The elastic conductive mechanism 43-2 can elastically deform under external force. Therefore, when the shaft 21 translates toward the proximal end, the shaft 21 applies pressure to the elastic conductive mechanism 43-2, causing compression and deformation. When the shaft translates toward the distal end, the pressure applied by the shaft 21 to the elastic conductive mechanism 43-2 is gradually released. Under the action of the elastic restoring force, the connection between the conductive connector 43-1 and the shaft 21 can be continuously maintained, maintaining a stable power supply to the circuit system 400. During this motion cycle, the elastic conductive mechanism 43-2 elastically deforms and reciprocates, overcoming the fatigue fracture or loosening of solder joints caused by the constant expansion and contraction of the wires during current wire connections. This not only maintains good controllability of the device, but also improves the reliability of the circuit.

[0041] The tissue ablation, cutting, and fusion system 900 further includes a temperature control component 401, which includes a temperature acquisition system 40-1 and a data transmission system 40-2. Temperature data collected by the temperature acquisition system 40-1 can be transmitted to the controller 42 via the data transmission system 40-2. The temperature acquisition system 40-1 can continuously acquire operating temperature data and transmit the acquired temperature data to the controller 42 via the data transmission system 40-2. The data processing system 42-2 in the controller 42 can monitor the acquired temperature in real time. When the acquired temperature exceeds a limit temperature set by the controller 42, the controller 42 can cut off power to the circuit 41 or adjust the current or voltage output by the power supply 500 via the data processing system 42-2, thereby reducing the operating temperature of the working portion 300. This effectively prevents accidental tissue damage or component damage caused by the electric heating device 32 being in a high temperature state for a long time, and provides greater safety during long-term operation.

[0042] The tissue ablation, cutting and fusion system 900 also includes a prompt system 600. The prompt system 600 can prompt the operator of the instrument's usage status as needed, such as using different sounds to indicate different working states, using different lights to indicate power status, and using different patterns to indicate different working areas.

[0043] The prompt system 600 is a sound prompt device 61, a light prompt device 62, or an image prompt device 63. The applicant only lists the above three prompt devices here, and those skilled in the art can design different prompt system structures as needed without departing from the scope of protection of this application.

[0044] The tissue ablation, cutting, and fusion system 900 also includes a smoke exhaust system 700, which includes a smoke outlet 71, a smoke exhaust pipe 72, and a smoke inlet 73. The smoke outlet 71 of the smoke exhaust system 700 can be connected to a medical negative pressure source to promptly extract smoke generated during surgery, ensuring a clear surgical field of view and making the surgical process safer and more reliable.

[0045] The tissue ablation, cutting, and fusion system 900 also includes a water supply / drainage system 800; this system includes a water outlet 81, a drain pipe 82, and a water inlet 83. The drain pipe 82 of the water supply / drainage system 800 can be either a drain pipe or a water supply pipe. During surgery, the surgeon can use the water supply / drainage system 800 to inject saline or other solvents into the surgical site as needed. The surgeon can also use the water supply / drainage system 800 to promptly remove blood or wastewater from the surgical site, ensuring a smooth surgical procedure.

[0046] During clinical use, the power supply 500 is connected to the circuit system 400 through the electrical interface 43-3, the power switch is turned on, the trigger 11-1 is pulled toward the handle 14-1, driving the inner rod 21-1 to move proximally, the working surface 31 is closed, the working part 300 clamps the tissue to be processed and continues to pull the trigger 11-1 until the force limiting mechanism 17 takes effect, turning on the trigger switch 42-1, and according to the surgical situation, the cutting gear 12-1 or the fusion gear 12-2 of the gear adjustment button 12 is selected to be pressed, and the gear adjustment button 12 turns on the controller 42. At this time, the circuit system 400 connects the power supply 500 and the electric heating device 32, and the electric heating device 32 starts to heat up. During this process, the elastic conductive mechanism 43-2 is elastically deformed under the thrust of the inner rod 21, maintaining stable power supply to the circuit system 400. At this time, the power supply 500 outputs a DC pulse voltage to the electric heating device 32, and periodically powers on and off the electric heating device 32. The electric heating device 32 is powered on for heating, and powered off for moderate cooling, and periodically changes its state. When powered on, the electric heating device 32 heats and heats up, and the heat is conducted through the body tissue to the deep part of the tissue or organ 9. After a certain period of high level, the power supply 500 switches to a low level state, and the electric heating device 32 is powered off and stops heating. At this time, the heat retained on the electric heating device 32 continues to be conducted through the body tissue, and the temperature of the electric heating device 32 is moderately reduced. Then the power supply 50 switches to a high level state again, and the electric heating device 32 heats and heats up again. This cyclical change of heating and moderate cooling can keep the temperature of the part where the electric heating device 32 contacts the tissue or organ 9 within a stable range while ensuring that heat is continuously conducted deep into the tissue or organ 9, and will not continue to rise, effectively avoiding accidental damage to the tissue or organ 9 caused by excessive temperature, and ensuring the safe and stable process of tissue ablation, cutting or fusion.

[0047] After the ablation, cutting, or fusion process is completed, the trigger 11-1 is released. The trigger 11-1 is reset by the reset mechanism 16, and the trigger switch 42-1 is disconnected. The electric heating device 32 ceases operation and ceases to generate heat. The inner rod 21-1 moves distally, and the working surface 32 opens, completing the tissue treatment process. To rotate the working surface 32, the knob 23 is simply rotated. This rotates the shaft 21, causing the working surface 32 connected to the shaft 21 to rotate accordingly. During rotation, the rotor 43-1-1 rotates synchronously with the shaft 21. This ensures synchronization between the conductive connector 43-1 and the circuit 41 at the rear end of the shaft 21. This prevents twisting of the circuit 41, which could cause wire breakage, loose solder joints, or heating of the connector. This ensures stable power supply to the circuit system 400. Different tissue parts are selected in turn, and the trigger 11-1 is repeatedly pulled and released to complete the surgical operation. The surgical operation is very simple.

[0048] At the same time, during clinical use, since the temperature acquisition system 40-1 can continuously collect working temperature data and transmit the collected temperature data to the controller 42 through the data transmission system 40-2, the data processing system 42-2 in the controller 42 can monitor the collected temperature in real time. When the collected temperature value exceeds the temperature value set by the controller 42, the controller 42 takes measures such as powering off the line 41 or adjusting the current or voltage output by the power supply 500 through the data processing system 42-2, so as to achieve the control effect of lowering the working temperature of the working part 300, effectively avoiding accidental damage to the tissue or accidental damage to the components caused by the electric heating device 32 being in a high temperature state for a long time, and being safer during long-term continuous operation.

[0049] The tissue ablation, cutting, and fusion system of the present invention includes a handle assembly 100, a shaft assembly 200, a working portion 300, a circuit system 400, and a power supply 500. The power supply 500 outputs a low-frequency DC pulse voltage with a high-level voltage below 24V and a frequency below 500Hz. The duty cycle of the DC pulse voltage output by the power supply 500 can be adjusted based on the thermal conductivity of the tissue to be ablated, cut, or fused. The DC pulse voltage output by the power supply 500 periodically switches between high and low levels to cyclically power on and off the electric heating device 32, maintaining the cyclical state of the electric heating device 32 between power on and power off for moderate cooling. This ensures that as heat is continuously transferred deep into the tissue or organ 9, the temperature at the site of contact between the heating device and the tissue or organ 9 remains within a stable range and does not continue to rise. This effectively prevents accidental damage to the tissue or organ 9 caused by excessive temperatures, making clinical use safer and more reliable. BRIEF DESCRIPTION OF THE DRAWINGS

[0050] Figure 1 It is a schematic diagram of the three-dimensional structure of a battery-type power source for a tissue ablation, cutting and fusion system according to the present invention.

[0051] Figure 2 It is a schematic diagram of the three-dimensional structure of a battery pack type power supply for a tissue ablation, cutting and fusion system of the present invention.

[0052] Figure 3 It is a schematic diagram of the three-dimensional structure of a power supply for a tissue ablation, cutting and fusion system according to the host type of the present invention.

[0053] Figure 4 It is a schematic diagram of the three-dimensional structure of the tissue ablation, cutting and fusion system of the present invention when the working surface is opened.

[0054] Figure 4-1 yes Figure 4 Schematic diagram of the three-dimensional structure when the working surface is closed.

[0055] Figure 5 yes Figure 1 main view.

[0056] Figure 5-1 yes Figure 5 AA cross-sectional view.

[0057] Figure 5-2 yes Figure 5-1 Enlarged view of point B.

[0058] Figure 6 yes Figure 4-1 main view.

[0059] Figure 6-1 yes Figure 6 CC cross-sectional view.

[0060] Figure 6-2 yes Figure 6-1 Enlarged view of point D.

[0061] Figure 7 It is a schematic structural diagram of the trigger assembly of the tissue ablation, cutting and fusion system of the present invention.

[0062] Figure 8 It is a schematic structural diagram of the shaft assembly of the tissue ablation, cutting and fusion system of the present invention.

[0063] Figure 8-1 yes Figure 8 EE cross-sectional view.

[0064] Figure 9 It is a schematic diagram of the three-dimensional structure of the tissue ablation, cutting and fusion system of the present invention including the water supply / drainage system.

[0065] Figure 9-1 yes Figure 9 Enlarged view of point F.

[0066] Figure 10 It is a schematic diagram of the three-dimensional structure of the tissue ablation, cutting and fusion system of the present invention including the clamping forceps.

[0067] Figure 10-1 yes Figure 10 Enlarged view of point G.

[0068] Figure 11 It is a schematic diagram of the three-dimensional structure of the tissue ablation, cutting and fusion system of the present invention with a battery and a battery pack.

[0069] Figure 12 It is a schematic diagram of the three-dimensional structure of the tissue ablation, cutting and fusion system of the present invention with a host.

[0070] Figure 13 It is a structural diagram of the working state of the tissue ablation, cutting and fusion system of the present invention.

[0071] Figure 13-1 yes Figure 13 Magnified image of .

[0072] Figure 14 It is the waveform of the DC pulse voltage with a high duty cycle.

[0073] Figure 14-1 It is the waveform of the DC pulse voltage with low duty cycle.

[0074] In the above figure:

[0075] 100 is a handle assembly, 200 is an axis assembly, 300 is a working part, 400 is a circuit system, 401 is a temperature control assembly, 500 is a power supply, 501 is a DC pulse power supply, 600 is a prompt system, 700 is a smoke exhaust system, 800 is a water supply / drainage system, 900 is the tissue ablation, cutting and fusion system of the present invention, and 9 is a tissue or organ.

[0076] On the handle assembly:

[0077] 11 is a trigger assembly, 12 is a gear adjustment button, 13 is an axis connection mechanism, 14 is a housing, 15 is a fixing mechanism, 16 is a reset mechanism, and 17 is a force limiting mechanism.

[0078] 11-1 is the trigger, 11-2 is the rocker arm, 11-3 is the slider; 11-1-1 is the trigger shaft, 11-1-2 is the rocker arm drive shaft, 11-1-3 is the trigger part, 11-2-1 is the rocker arm fulcrum, 11-2-2 is the motion slide groove, 11-2-3 is the push block slot, 11-3-1 is the motion push block, 11-3-2 is the sliding convex step, and 11-3-3 is the working boss.

[0079] 12-1 is the cutting gear, 12-2 is the fusion gear, and 12-3 is the lever mechanism.

[0080] 14-1 is the handle.

[0081] 15-1 is a positioning chute.

[0082] 17-1 is a spring force limiting mechanism.

[0083] On the shaft assembly:

[0084] 21 is a shaft, 22 is a connecting assembly, and 23 is a knob.

[0085] 21-1 is the inner rod and 21-2 is the outer rod.

[0086] Work Department:

[0087] 31 is a working surface, 32 is an electric heating device, 33 is a rotating shaft; 31-1 is a distal working surface, 31-2 is a proximal working surface; 301 is a first working part, 302 is a second working part.

[0088] On the circuit system:

[0089] 41 is a circuit, 42 is a controller, 43 is an electrical interface device, 44 is an insulating layer, and 431 is an elastic electrical interface device.

[0090] 41-1 is a conductive core rod, 42-1 is a trigger switch, 42-2 is a data processing system, 43-1 is a conductive connector, 43-2 is an elastic conductive mechanism, 43-3 is an electrical interface; 43-1-1 is a rotor, 43-1-2 is a stator; brush 43-11.

[0091] On the temperature control assembly:

[0092] 40-1 is the temperature acquisition system, and 40-2 is the data transmission system.

[0093] On the power supply:

[0094] 51 is a battery module, 52 is a battery pack module, and 53 is a host.

[0095] On the prompt system:

[0096] 61 is a sound prompt device, 62 is a light prompt device, and 63 is an image prompt device.

[0097] On the smoke exhaust system:

[0098] 71 is the smoke outlet, 72 is the smoke exhaust pipe, and 73 is the smoke inlet.

[0099] On the water supply / drainage system:

[0100] 81 is the water outlet, 82 is the drain pipe, and 83 is the water inlet. DETAILED DESCRIPTION

[0101] Example 1: A power supply for a tissue ablation, cutting, and fusion system according to the present invention

[0102] refer to Figures 1 to 3 In this embodiment, a power supply for a tissue ablation, cutting, and fusion system is a low-voltage power supply having an output voltage less than 24 V. Preferably, the output voltage of the power supply 500 is less than 12 V.

[0103] The output voltage of the power supply 500 is a safe voltage less than 24V, and even if an accidental phenomenon such as leakage occurs during use, it will not cause accidental harm to the human body.

[0104] In this embodiment, the power supply 500 is a DC pulse power supply 501, which outputs a DC pulse voltage. The DC pulse voltage output by the power supply 500 periodically switches between high and low levels to periodically power on and off the electric heating device 32, maintaining the electric heating device 32 in a state of power on for heating and power off for moderate cooling. This ensures that as heat is continuously conducted deep into the tissue or organ 9, the temperature of the area where the heating device contacts the tissue or organ 9 remains within a stable range and does not continue to rise, effectively preventing accidental damage to the tissue or organ 9 due to excessive temperature, making clinical use safer and more reliable.

[0105] refer to Figure 14 and Figure 14-1 In this embodiment, based on the thermal conductivity of tissues and organs, the frequency of the DC pulse voltage output by the DC pulse power supply 501 is less than 500 Hz. Preferably, the frequency range of the DC pulse voltage output by the DC pulse power supply 501 is 3 Hz to 200 Hz. Low-frequency pulses can expand the range of high-level and low-level durations, ensuring sufficient heat conduction time while also giving the heating device 32 sufficient cooling time to ensure that the temperature of the heating device 32 can be controlled within a safe temperature range. At the same time, low-frequency pulses can better avoid electromagnetic interference that may be caused by electromagnetic pulses on peripheral equipment during instrument operation, thereby improving the electromagnetic compatibility of the instrument.

[0106] In this embodiment, the duty cycle of the DC pulse voltage output by the DC pulse power supply 501 can be adjusted according to the different thermal conductivity coefficients of the tissue or organ 9 that needs to be ablated, cut, or fused.

[0107] Depending on the thermal conductivity of the tissue being ablated, cut, or fused, the required power output of the heating device 32 also varies. Consequently, the duty cycle of the DC pulse voltage output by the DC pulse power supply 501 also varies. This means that the heating time and power-off time of the heating device 32 need to be adjustable based on the target tissue. The duty cycle of the DC pulse voltage output by the power supply for a tissue ablation, cutting, and fusion system of the present invention is adjustable to meet the thermal conductivity requirements of different tissues or organs 9.

[0108] The output current of the power supply 500 is less than 10A.

[0109] refer to Figure 11 and Figure 12The power source 500 can be a battery module 51, a battery pack module 52, or a main unit 53. The battery module 51 or battery pack module 52 is small in size and light in weight, suitable for carrying outside, has low requirements for the power environment, and low voltage power supply is safer. The main unit 53 can provide stable power supply for a long time, which is particularly suitable for large-scale surgery with long operating time. Users can choose different power sources 500 according to different usage environments and requirements.

[0110] refer to Figure 13 In this embodiment, a power supply for a tissue ablation, cutting and fusion system outputs a low-frequency DC pulse voltage with a high-level voltage lower than 24V and a frequency lower than 500Hz. Through the periodic alternation of high and low levels, the electric heating device 32 is periodically powered on and off, and the electric heating device 32 is kept powered on for heating and powered off for moderate cooling. In this way, while heat is continuously conducted deep into the tissue or organ 9, the temperature of the part where the heating device contacts the tissue or organ 9 is maintained within a stable range and does not continue to rise, thereby effectively avoiding accidental damage to the tissue or organ 9 caused by excessive temperature, and making the clinical use process safer and more reliable.

[0111] Example 2: Tissue ablation, cutting and fusion system of the present invention

[0112] refer to Figures 4 to 9-1 The tissue ablation, cutting and fusion system of this embodiment includes the power supply 500 described in Example 1.

[0113] The tissue ablation, cutting and fusion system of this embodiment includes a handle assembly 100 , a shaft assembly 200 , a working portion 300 , a circuit system 400 , a power supply 500 , a prompt system 600 and a smoke exhaust system 700 .

[0114] In this embodiment, the power supply 500 adopts a host 53 that can provide stable power for a long time. The host 53 outputs a low-frequency DC pulse voltage with a high-level voltage lower than 24V and a frequency lower than 500Hz.

[0115] The handle assembly 100 includes a trigger assembly 11, a gear adjustment button 12, a shaft connection mechanism 13, a housing 14, a fixing mechanism 15, a reset mechanism 16, and a force limiting mechanism 17. The trigger assembly 11 is fixedly mounted on the housing 14 via the fixing mechanism 15, and the gear adjustment button 12 and the shaft connection mechanism 13 are provided on the housing 14.

[0116] The shaft assembly 200 includes a shaft 21 , a connecting assembly 22 and a knob 23 .

[0117] The working portion 300 includes two working surfaces 31 , and an electric heating device 32 is provided on one of the working surfaces 31 .

[0118] The circuit system 400 includes a circuit 41, a controller 42, and an electrical interface device 43. The circuit system 400 is connected to the power supply 500 via the electrical interface device 43.

[0119] In this embodiment, the controller 42 includes a trigger switch 42 - 1 ; movement of the trigger assembly 11 can turn the trigger switch 42 - 1 on or off.

[0120] The proximal end of the shaft assembly 200 is connected to the handle assembly 100 via the shaft connection mechanism 13 ; the distal end of the shaft assembly 200 is connected to the working part 300 ; and the electric heating device 32 is connected to the power source 500 via the circuit system 400 .

[0121] refer to Figure 6 and Figure 7 The trigger assembly 11 includes a trigger 11-1, a rocker arm 11-2 and a slider 11-3; the trigger 11-1 is provided with a trigger shaft 11-1-1 and a rocker arm drive shaft 11-1-2; the rocker arm 11-2 includes a rocker arm fulcrum 11-2-1, a motion slide 11-2-2 and a push block slot 11-2-3; the slider 11-3 includes a motion push block 11-3-1, a sliding convex step 11-3-2 and a working boss 11-3-3; the trigger shaft 11-1-1 and the fixing mechanism 15 are connected together and fixed on the housing 14; one end of the rocker arm drive shaft 11-1-2 is connected to the trigger 11-1, and the other end is embedded in the motion slide 11-2-2; the rocker arm fulcrum 11-2-1 and the fixing mechanism 15 are connected together to movably mount the rocker arm 11-2 Installed in the shell 14; the motion push block 11-3-1 is embedded in the push block slot 11-2-3, and the sliding cam 11-3-2 is embedded in the positioning slot 15-1 of the fixing mechanism 15, and is connected to the fixing mechanism 15; when the trigger 11-1 is pulled, the trigger 11-1 rotates around the trigger shaft 11-1-1, driving the rocker drive shaft 11-1-2 to reciprocate along the motion slot 11-2-2, thereby pushing the rocker arm 11-2 to swing back and forth around the rocker arm fulcrum 11-2-1; the reciprocating swing of the rocker arm 11-2 pushes the motion push block 11-3-1 embedded in the push block slot 11-2-3, thereby driving the slider to move back and forth in a straight line along the positioning slot 15-1, thereby realizing the closing and opening of the working surface 31 of the working part 300.

[0122] A trigger portion 11-1-3 is provided on the trigger 11-1; when the trigger 11-1 moves toward the handle 14-1 of the shell 14, the trigger portion 11-1-3 touches the trigger switch 42-1, and the trigger switch 42-1 is turned on; when the trigger 11-1 moves away from the handle 14-1 of the shell 14, the trigger portion 11-1-3 disengages from the trigger switch 42-1, and the trigger switch 42-1 is turned off.

[0123] The gear adjustment button 12 is connected to the controller 42 via the line 41. Doctors can select different output powers through the gear adjustment button 12 according to the specific circumstances of the surgical process, making clinical operation more convenient.

[0124] In this embodiment, the gear adjustment button 12 includes a cutting gear 12-1 and a fusion gear 12-2; the cutting gear 12-1 and the fusion gear 12-2 are linked together by a lever mechanism 12-3, so that the cutting gear 12-1 and the fusion gear 12-2 cannot be pressed simultaneously. This prevents the cutting gear 12-1 and the fusion gear 12-2 from being pressed simultaneously, thereby preventing misoperation during clinical use.

[0125] In this embodiment, the handle assembly 100 includes a reset mechanism 16. In this embodiment, the reset mechanism 16 is a combination of a torsion spring mechanism 16-1 and a spring mechanism 16-2. The torsion spring mechanism 16-1 is disposed at the trigger shaft 11-1-1, and the spring mechanism 16-2 is disposed proximal to the positioning slot 15-1 of the fixing mechanism 15. When the trigger 11-1 is pulled, the torsion spring mechanism 16-1 is compressed, the inner rod 21-1 moves proximally, and the spring mechanism 16-2 is compressed and deformed. When the trigger 11-1 is released, the inner rod 21-1 moves distally under the action of the torsion spring mechanism 16-1 and the spring mechanism 16-2, and the trigger 11-1 automatically resets.

[0126] Those skilled in the art may also design various reset mechanisms as needed, and install one or more reset mechanisms 16 at different locations of the instrument as needed, without departing from the scope of protection of this application.

[0127] In this embodiment, the handle assembly 100 includes a force-limiting mechanism 17. The force-limiting mechanism 17 can limit the operating pressure transmitted to the working portion 300 via the trigger assembly 11. When the force-limiting mechanism 17 is activated, the maximum operating pressure applied to the working portion 300 by the operator pulling the trigger 11-1 is constant. Typically, during soft tissue ablation, cutting, and fusion procedures, the maximum operating pressure can be limited to less than 100 N. Of course, those skilled in the art can adjust the maximum operating pressure limit of the force-limiting mechanism 17 as needed without departing from the scope of protection of this application.

[0128] In this embodiment, the trigger 11-1 is moved toward the handle 14-1 of the housing 14 until the force-limiting mechanism 17 activates the trigger switch 42-1. Only when the trigger switch 42-1 is engaged can the gear adjustment button 12 be closed, energizing the circuit system 400 and enabling the tissue ablation, cutting, or fusion system 900 to perform tissue ablation, cutting, or fusion at the set operating pressure. Because the trigger switch 42-1 is only activated when the force-limiting mechanism 17 activates, the operating pressure applied to the tissue by the surgeon during surgery is constant, thereby avoiding variations in surgical results due to varying operating pressures applied by different operators. This provides more stable surgical results and effectively avoids potential safety hazards caused by continued heating of the electric heating device 32 in the non-operating state, resulting in a safer and more reliable surgical procedure. Of course, those skilled in the art may also design the trigger switch 42-1 to be engaged in different states as needed, without departing from the scope of protection of this application.

[0129] In this embodiment, the force limiting mechanism 17 is a spring force limiting mechanism 17-1, which is arranged at the proximal end of the working boss 11-3-3 of the slider 11-3. When the inner rod 21-1 moves toward the proximal end, the working boss 11-3-3 presses the spring force limiting mechanism 17-1, and the spring force limiting mechanism 17-1 undergoes elastic deformation, thereby achieving the effect of limiting the working pressure.

[0130] Those skilled in the art may also design various other forms of force limiting mechanisms such as an elastic force limiting mechanism or a compression spring force limiting mechanism, which do not depart from the scope of protection of this application.

[0131] During clinical use, the working surface 31 often needs to be rotated to a suitable position according to the different parts of the tissue to be treated. Therefore, in this embodiment, the shaft assembly 200 includes a knob 23, and the knob 23 can drive the shaft 21 to rotate.

[0132] The shaft 21 includes an inner rod 21-1 and an outer rod 21-2. The working surface 31 is connected to the distal ends of the inner rod 21-1 and the outer rod 21-2, respectively. When the inner rod 21-1 moves toward the proximal end, the working surface 31 closes; when the inner rod 21-1 moves toward the distal end, the working surface 31 opens. Turning the knob 23 rotates the inner rod 21-1 and the outer rod 21-2, thereby driving the working surface 31 to rotate.

[0133] In this embodiment, the electrical interface device 43 is an elastic electrical interface device 431, which includes a conductive connector 43-1, an elastic conductive mechanism 43-2, and an electrical interface 43-3. One end of the conductive connector 43-1 is connected to the electric heating device 32 via the circuit 41, and the other end is connected to the elastic conductive mechanism 43-2. The other end of the elastic conductive mechanism 43-2 is connected to the electrical interface 43-3, and the electrical interface 43-3 is connected to the power source 500.

[0134] The conductive joint 43-1 includes a rotor 43-1-1 and a stator 43-1-2; the rotor 43-1-1 can rotate; the distal end of the rotor 43-1-1 is connected to the proximal end of the shaft 21, and when the shaft 21 rotates, the rotor 43-1-1 can rotate synchronously; the proximal end of the stator 43-1-2 is connected to the distal end of the elastic conductive mechanism 43-2.

[0135] Since the rotor 43-1-1 can rotate synchronously with the shaft 21, the line 41 connecting the rotor 43-1-1 and the shaft 21 also rotates synchronously. The line 41 connecting the conductive connector 43-1 and the rear end of the shaft 21 remains synchronized, thereby avoiding the possible breakage of the wires, loosening of the solder joints, or heating of the connectors caused by the twisting of the line 41.

[0136] The elastic conductive mechanism 43-2 is a conductive mechanism that can undergo elastic deformation under the action of external force while maintaining a smooth circuit. The elastic conductive mechanism 43-2 can undergo elastic deformation under the action of external force. Therefore, when the shaft 21 translates toward the proximal end, the shaft 21 applies pressure to the elastic conductive mechanism 43-2, causing the elastic conductive mechanism 43-2 to compress and deform. When the shaft translates toward the distal end, the pressure applied by the shaft 21 to the elastic conductive mechanism 43-2 is gradually released. Under the action of the elastic restoring force, the connection between the conductive connector 43-1 and the shaft 21 can be continuously maintained, maintaining a stable power supply to the circuit system 400. During this motion cycle, the elastic conductive mechanism 43-2 undergoes elastic deformation and performs a reciprocating motion, overcoming the fatigue fracture, loose solder joints, or heating of the connectors caused by the constant expansion and contraction of the wires during current wire connections. This not only maintains good controllability of the instrument, but also improves the reliability of the circuit.

[0137] In this embodiment, the elastic conductive mechanism 43-2 is a coil spring mechanism. The elastic conductive mechanism 43-2 may also be a pyramidal spring mechanism, a compression spring mechanism, or other spring mechanisms, which the applicant does not enumerate here. Those skilled in the art may also design the elastic conductive mechanism 43-2 into other elastic structures such as an elastomer structure as needed, without departing from the scope of protection of the present invention.

[0138] In this embodiment, the specific circuit connection method is as follows:

[0139] Positive electrode circuit: The positive electrode of the electric heating device 32 is connected to the circuit 41 arranged in the rod core of the inner rod 21-1. In order to enhance the strength of the inner rod 21-1 during the translation and clamping process, this part of the circuit 41 is arranged as a rigid conductive core rod 41-1. An insulating layer 44 is provided between the conductive core rod 41-1 and the inner rod 21-1. One end of the conductive core rod 41-1 is connected to the positive electrode of the electric heating device 32, and the other end is connected to the positive electrode of the rotor 43-1-1. The other end of the positive electrode of the rotor 43-1-1 is connected to the positive electrode of the stator 43-1-2 by means of a brush. The other end of the positive electrode of the stator 43-1-2 is connected to the positive electrode of the elastic conductive mechanism 43-2. The other end of the positive electrode of the elastic conductive mechanism 43-2 is connected to the positive electrode of the electrical interface 43-3, and is connected to the positive electrode of the power supply 500 via the electrical interface 43-3.

[0140] Negative pole circuit: The negative pole of the electric heating device 32 is connected to the distal end of the conductive inner rod 21-1, and an insulating layer 44 is provided between the inner rod 21-1 and the outer rod 21-2. The proximal end of the inner rod 21-1 is connected to the negative pole of the rotor 43-1-1 via the circuit 41, and the other end of the negative pole of the rotor 43-1-1 is connected to the negative pole of the stator 43-1-2 by means of a brush, and the other end of the negative pole of the stator 43-1-2 is connected to the negative pole of the elastic conductive mechanism 43-2, and the other end of the negative pole of the elastic conductive mechanism 43-2 is connected to the negative pole of the electrical interface 43-3, and is connected to the negative pole of the power supply 500 via the electrical interface 43-3.

[0141] In this embodiment, the working current flows in through the positive electrode of the electrical interface 43-3, passes through the elastic conductive mechanism 42, flows into the stator 43-1-2 through the positive electrode of the stator 43-1-2, flows out of the stator 43-1-2, flows into the rotor 43-1-1 through the positive electrode of the rotor 43-1-1, flows out of the rotor 43-1-1, flows into the conductive core rod 41-1 from the proximal end of the conductive core rod 41-1, flows through the conductive core rod 41-1, enters the electric heating device 32 from the positive electrode of the electric heating device 32, drives the electric heating device 32 to generate heat, and the electric current flows out of the rotor 43-1-1. The current then flows out from the negative pole of the electric heating device 32 and enters the distal end of the inner rod 21-1, flows through the inner rod 21-1 and flows out from the proximal end of the inner rod 21-1, and enters the negative pole of the rotor 43-1-1, flows out from the negative pole of the rotor 43-1-1 and enters the negative pole of the stator 43-1-2, enters the elastic conductive mechanism 43-2 after passing through the stator 43-1-2, flows through the elastic conductive mechanism 43-2 and flows into the electrical interface 43-3 from the distal end of the elastic conductive mechanism 43-2, and flows into the negative pole of the power supply 500 after passing through the electrical interface 43-3.

[0142] In this embodiment, the tissue ablation, cutting, and fusion system 900 further includes a temperature control component 401; the temperature control component 401 includes a temperature acquisition system 40-1 and a data transmission system 40-2; the temperature data collected by the temperature acquisition system 40-1 can be transmitted to the controller 42 via the data transmission system 40-2. The temperature acquisition system 40-1 can continuously collect operating temperature data and transmit the collected temperature data to the controller 42 via the data transmission system 40-2. The data processing system 42-2 in the controller 42 can monitor the collected temperature in real time. When the collected temperature value exceeds the limit temperature value set by the controller 42, the controller 42 can take measures such as powering off the circuit 41 or adjusting the current or voltage output by the power supply 500 through the data processing system 42-2 to achieve the control effect of lowering the operating temperature of the working part 300, effectively avoiding accidental tissue damage or component damage caused by the electric heating device 32 being in a high temperature state for a long time, and improving safety during long-term operation.

[0143] refer to Figure 5-1 and Figure 12 The tissue ablation, cutting, and fusion system of this embodiment includes a prompt system 600. The prompt system 600 can prompt the operator of the instrument's usage status as needed, such as using different sounds to indicate different working states, using different lights to indicate power status, and using different patterns to indicate different working areas.

[0144] In this embodiment, the prompt system 600 includes three prompt devices: a sound prompt device 61, a light prompt device 62, and an image prompt device 63. Those skilled in the art can design different prompt system structures as needed without departing from the scope of protection of this application.

[0145] In this embodiment, the tissue ablation, cutting, and fusion system 900 includes a smoke exhaust system 700. The smoke exhaust system 700 includes a smoke outlet 71, a smoke exhaust pipe 72, and a smoke inlet 73. The smoke outlet 71 of the smoke exhaust system 700 can be connected to a medical negative pressure source to promptly extract smoke generated during surgery, ensuring a clear surgical field of view and making the surgical procedure safer and more reliable.

[0146] refer to Figure 9The tissue ablation, cutting and fusion system of the present invention may also include a water supply / drainage system 800. The water supply / drainage system 800 includes a water outlet 81, a drain pipe 82 and a water inlet 83. The drain pipe 82 of the water supply / drainage system 800 can be either a drain pipe or a water supply pipe. During the operation, the doctor can inject physiological saline or other solvents into the surgical site through the water supply / drainage system 800 according to the needs of the operation, or can use the water supply / drainage system 800 to promptly remove blood or sewage from the surgical site to ensure a smooth operation. At the same time, the water supply / drainage system 800 can also be used as the smoke exhaust system 700 to promptly remove the smoke generated during the operation to ensure a clear surgical field of view.

[0147] During clinical use, the power supply 500 is connected to the circuit system 400 through the electrical interface 43-3, the power switch is turned on, the trigger 11-1 is pulled to move toward the handle 14-1, driving the inner rod 21-1 to move proximally, the working surface 31 is closed, the working part 300 clamps the tissue to be treated and continues to pull the trigger 11-1 until the force limiting mechanism 17 takes effect, and the trigger switch 42-1 is turned on. According to the surgical situation, the cutting gear 12-1 or the fusion gear 12-2 of the gear adjustment button 12 is selected to be pressed, and the gear adjustment button 12 turns on the controller 42. At this time, the circuit system 400 connects the power supply 500 and the electric heating device 32, and the electric heating device 32 starts to heat up to ablate, cut or fuse the tissue. During this process, the elastic conductive mechanism 43-2 is elastically deformed under the thrust of the inner rod 21 to maintain stable power supply to the circuit system 400.

[0148] At this time, the power supply 500 outputs a DC pulse voltage to the electric heating device 32, and periodically powers on and off the electric heating device 32. The electric heating device 32 is powered on for heating, and powered off for moderate cooling, and periodically changes its state. When powered on, the electric heating device 32 heats and heats up, and the heat is conducted through the body tissue to the deep part of the tissue or organ 9. After a certain period of high level, the power supply 500 switches to a low level state, and the electric heating device 32 is powered off and stops heating. At this time, the heat retained on the electric heating device 32 continues to be conducted through the body tissue, and the temperature of the electric heating device 32 is moderately reduced. Then the power supply 50 switches to a high level state again, and the electric heating device 32 heats and heats up again. This cyclical change of heating and moderate cooling can keep the temperature of the part where the electric heating device 32 contacts the tissue or organ 9 within a stable range while ensuring that heat is continuously conducted deep into the tissue or organ 9, and will not continue to rise, effectively avoiding accidental damage to the tissue or organ 9 caused by excessive temperature, and ensuring the safe and stable process of tissue ablation, cutting or fusion.

[0149] After the procedure is completed, the trigger 11-1 is released. The reset mechanism 16 resets the trigger 11-1, disengaging the trigger switch 42-1. The electric heater 32 ceases operation and ceases heating. The inner rod 21-1 moves distally, opening the working surface 32 and completing the tissue treatment procedure. To rotate the working surface 32, the knob 23 is simply rotated. This rotates the shaft 21, causing the working surface 32 connected to the shaft 21 to rotate accordingly. During rotation, the rotor 43-1-1 rotates synchronously with the shaft 21. This ensures synchronization between the conductive connector 43-1 and the circuit 41 at the rear end of the shaft 21. This prevents twisting of the circuit 41, which could cause wire breakage, loose solder joints, or heating. This ensures stable power supply to the circuit system 400. By selecting different tissue sites and repeatedly pulling and releasing the trigger 11-1, the surgical procedure is completed, making the operation very simple.

[0150] At the same time, during clinical use, since the temperature acquisition system 40-1 can continuously collect working temperature data and transmit the collected temperature data to the controller 42 through the data transmission system 40-2, the data processing system 42-2 in the controller 42 can monitor the collected temperature in real time. When the collected temperature value exceeds the temperature value set by the controller 42, the controller 42 takes measures such as powering off the line 41 or adjusting the current or voltage output by the power supply 500 through the data processing system 42-2, so as to achieve the control effect of lowering the working temperature of the working part 300, effectively avoiding accidental damage to the tissue or accidental damage to the components caused by the electric heating device 32 being in a high temperature state for a long time, and being safer during long-term continuous operation.

[0151] In this embodiment, the trigger 11-1 moves toward the handle 14-1 of the shell 14 until the force limiting mechanism 17 takes effect, and the trigger part 11-1-3 touches the trigger switch 42-1, and the trigger switch 42-1 is turned on; when the trigger 11-1 moves away from the handle 14-1 of the shell 14, the trigger part 11-1-3 disengages from the trigger switch 42-1, and the trigger switch 42-1 is turned off. Because the trigger switch 42-1 can be activated only when the force-limiting mechanism 17 takes effect, the tissue ablation, cutting and fusion system of the present invention can only perform tissue ablation, cutting or fusion under the set working pressure, the surgical effect is more stable, and the accidental injury caused by misoperation and the clinical effect differences such as blood vessel closure, tissue fusion, cutting, etc. caused by different clamping forces used by different surgeons are effectively prevented. It is safer and more effective. That is, a tissue ablation, cutting and fusion system of the present invention can only be activated to perform tissue ablation, cutting and fusion under a constant clamping force, avoiding the difference in use effect caused by different forces used by operators.

[0152] In this embodiment, the closing of the working surfaces 31 is achieved by translating one working surface 31 toward another working surface 31 .

[0153] refer to Figure 10 and Figure 10-1In actual applications, the two working surfaces 31 can also be closed by rotating the working surfaces 31 around the rotation axis 33. The working part 300 includes a first working part 301 and a second working part 302; the proximal end of the first working part 301 is connected to the distal end of the inner rod 21-1, and the proximal end of the second working part 302 is connected to the distal end of the outer rod 21-2. When the inner rod 21-1 moves toward the proximal end, it drives the first working part 301 to rotate around the rotation axis 33, and the first working part 301 and the second working part 302 are closed. With this working part design, the working part 300 is very small in the closed state and can enter the abdominal cavity through a very small channel. The working part 300 can then be opened for surgical operations. It is particularly suitable for use in various endoscopic minimally invasive surgeries.

[0154] It should be noted that the structures disclosed and described herein may be replaced by other structures with equivalent effects, and the embodiments described herein are not the only structures for implementing the present invention. Although preferred embodiments of the present invention have been described and illustrated herein, those skilled in the art will readily appreciate that these embodiments are merely illustrative and that numerous variations, modifications, and substitutions may be made by those skilled in the art without departing from the present invention. Therefore, the scope of protection of the present invention should be defined in accordance with the spirit and scope of the appended claims.

Claims

1. Tissue ablation, cutting and fusion system, characterized by: A. The tissue ablation, cutting and fusion system (900) comprises a handle assembly (100), a shaft assembly (200), a working portion (300), a circuit system (400), a temperature control assembly (401), and a power supply (500); B. The power supply (500) is a low-voltage DC pulse power supply (501) with an output voltage less than 24V. The duty cycle of the DC pulse voltage output by the DC pulse power supply (501) can be adjusted according to the different thermal conductivity coefficients of the tissue or organ (9) to be ablated, cut, or fused. C. The handle assembly (100) includes a trigger assembly (11), a gear adjustment button (12), a shaft connection mechanism (13), and a housing (14); the trigger assembly (11), the gear adjustment button (12), and the shaft connection mechanism (13) are arranged on the housing (14); D. The shaft assembly (200) comprises a shaft (21) and a connecting assembly (22); E. The working portion (300) comprises at least two working surfaces (31), and at least one of the working surfaces (31) is provided with an electric heating device (32); F. The circuit system (400) includes a circuit (41), a controller (42) and an electrical interface device (43); the circuit system (400) is connected to the power supply (500) via the electrical interface device (43); the electrical interface device (43) is an elastic electrical interface device (431), and the elastic electrical interface device (431) includes a conductive connector (43-1), an elastic conductive mechanism (43-2) and an electrical interface (43-3); the conductive connector (43-1) includes a rotor (43-1-1) and a stator (43-1-2); the rotor (43-1-1) is capable of rotating; the distal end of the rotor (43-1-1) and the proximal end of the shaft (21) are connected together. When the shaft (21) rotates, the rotor (43-1-1) can rotate synchronously; the proximal end of the stator (43-1-2) is connected to the distal end of the elastic conductive mechanism (43-2); the elastic conductive mechanism (43-2) is a conductive mechanism that can undergo elastic deformation under the action of an external force while maintaining a smooth circuit; one end of the conductive connector (43-1) is connected to the electric heating device (32) through the line (41), and the other end is connected to the elastic conductive mechanism (43-2); the other end of the elastic conductive mechanism (43-2) is connected to the electrical interface (43-3), and the electrical interface (43-3) is connected to the power supply (500); G. The temperature control component (401) includes a temperature acquisition system (40-1) and a data transmission system (40-2); the temperature data acquired by the temperature acquisition system (40-1) can be transmitted to the controller (42) via the data transmission system (40-2); H. The proximal end of the shaft assembly (200) is connected to the handle assembly (100) via the shaft connection mechanism (13); the distal end of the shaft assembly (200) is connected to the working part (300); and the electric heating device (32) is connected to the power source (500) via the circuit system (400).

2. The tissue ablation, cutting and fusion system according to claim 1, characterized in that: The output voltage of the power supply (500) is less than 12V.

3. The tissue ablation, cutting and fusion system according to claim 1, characterized in that: The frequency of the DC pulse voltage output by the DC pulse power supply (501) is less than 500 Hz.

4. The tissue ablation, cutting and fusion system according to claim 3, characterized in that: The frequency range of the DC pulse voltage output by the DC pulse power supply (501) is 3 Hz to 200 Hz.

5. The tissue ablation, cutting and fusion system according to claim 1, characterized in that: The output current of the power supply (500) is less than 10A.

6. The tissue ablation, cutting and fusion system according to claim 1, characterized in that: The power source (500) is a battery module (51).

7. The tissue ablation, cutting and fusion system according to claim 1, characterized in that: The controller (42) includes a trigger switch (42-1); the movement of the trigger assembly (11) can turn the trigger switch (42-1) on or off.

8. The tissue ablation, cutting and fusion system according to claim 1, characterized in that: The handle assembly (100) further includes a fixing mechanism (15); the trigger assembly (11) is fixedly mounted on the housing (14) via the fixing mechanism (15).

9. The tissue ablation, cutting and fusion system according to claim 8, characterized in that: The trigger assembly (11) includes a trigger (11-1), a rocker arm (11-2) and a slider (11-3); the trigger (11-1) is provided with a trigger shaft (11-1-1) and a rocker arm drive shaft (11-1-2); the rocker arm (11-2) includes a rocker arm fulcrum (11-2-1), a motion slide groove (11-2-2) and a push block slot (11-2-3); the slider (11-3) includes a motion push block (11-3-1), a sliding convex step (11- 3-2) and a working boss (11-3-3); the trigger shaft (11-1-1) and the fixing mechanism (15) are connected together and fixed to the housing (14); one end of the rocker arm drive shaft (11-1-2) is connected to the trigger (11-1), and the other end is embedded in the motion slot (11-2-2); the rocker arm fulcrum (11-2-1) and the fixing mechanism (15) are connected together to enable the rocker arm (11-2) to move The movable push block (11-3-1) is embedded in the push block slot (11-2-3), and the sliding convex step (11-3-2) is embedded in the positioning slot (15-1) of the fixing mechanism (15) and connected to the fixing mechanism (15); when the trigger (11-1) is pulled, the trigger (11-1) rotates around the trigger shaft (11-1-1), driving the rocker drive shaft (11-1 -2) reciprocates along the motion slide groove (11-2-2), thereby pushing the rocker arm (11-2) to swing back and forth around the rocker arm fulcrum (11-2-1); the reciprocating swing of the rocker arm (11-2) pushes the motion push block (11-3-1) embedded in the push block slot (11-2-3), thereby driving the slider to move back and forth linearly along the positioning slide groove (15-1), thereby realizing the closing and opening of the working surface (31) of the working part (300).

10. The tissue ablation, cutting and fusion system according to claim 7, characterized in that: A trigger portion (11-1-3) is provided on the trigger (11-1); when the trigger (11-1) moves toward the grip (14-1) of the housing (14), the trigger portion (11-1-3) touches the trigger switch (42-1), and the trigger switch (42-1) is turned on; when the trigger (11-1) moves away from the grip (14-1) of the housing (14), the trigger portion (11-1-3) disengages from the trigger switch (42-1), and the trigger switch (42-1) is turned off.

11. The tissue ablation, cutting and fusion system according to claim 1, characterized in that: The gear adjustment button (12) is connected to the controller (42) via the line (41).

12. The tissue ablation, cutting and fusion system according to claim 1, characterized in that: The gear adjustment button (12) includes a cutting gear (12-1) and a fusion gear (12-2); the cutting gear (12-1) and the fusion gear (12-2) are linked together via a lever mechanism (12-3), so that the cutting gear (12-1) and the fusion gear (12-2) cannot be pressed simultaneously.

13. The tissue ablation, cutting and fusion system according to claim 1, characterized in that: The handle assembly (100) further comprises a reset mechanism (16).

14. The tissue ablation, cutting and fusion system according to claim 7, characterized in that: The handle assembly (100) further comprises a force limiting mechanism (17).

15. The tissue ablation, cutting and fusion system according to claim 14, characterized in that: The trigger (11-1) moves toward the handle (14-1) of the housing (14) until the force-limiting mechanism (17) takes effect, and then the trigger switch (42-1) can be activated. When the trigger switch (42-1) is in the on state, the gear adjustment button (12) can be closed, and the circuit system (400) can be connected, so that the tissue ablation, cutting and fusion system (900) can perform tissue ablation, cutting or fusion under the set working pressure.

16. The tissue ablation, cutting and fusion system according to claim 1, characterized in that: The shaft assembly (200) further includes a knob (23); the knob (23) is capable of driving the shaft (21) to perform rotational motion.

17. The tissue ablation, cutting and fusion system according to claim 16, characterized in that: The shaft (21) includes an inner rod (21-1) and an outer rod (21-2); the working surface (31) is connected to the distal ends of the inner rod (21-1) and the outer rod (21-2), respectively; when the inner rod (21-1) moves toward the proximal end, the working surface (31) is closed; when the inner rod (21-1) moves toward the distal end, the working surface (31) is opened; and rotating the knob (23) can drive the inner rod (21-1) and the outer rod (21-2) to rotate, thereby driving the working surface (31) to perform rotational movement.

18. The tissue ablation, cutting and fusion system according to claim 1, characterized in that: The tissue ablation, cutting and fusion system (900) also includes a prompting system (600).

19. The tissue ablation, cutting and fusion system according to claim 18, characterized in that: The prompting system (600) is a sound prompting device (61), or a light prompting device (62), or an image prompting device (63).

20. The tissue ablation, cutting and fusion system according to claim 1, characterized in that: The tissue ablation, cutting and fusion system (900) further includes a smoke exhaust system (700); the smoke exhaust system (700) includes a smoke outlet (71), a smoke exhaust pipe (72) and a smoke inlet (73).

21. The tissue ablation, cutting and fusion system according to claim 1, characterized in that: The tissue ablation, cutting and fusion system (900) further includes a water supply / drainage system (800); the water supply / drainage system (800) includes a water outlet (81), a drainage pipe (82) and a water inlet (83).

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